Portable ultrasound imaging probe including a transducer array

ABSTRACT

A portable ultrasonic imaging probe that is adapted to connect to a host computer via a passive interface cable. The probe includes an array of ultrasound transducers, a high voltage pulser for energizing transducers to emit an ultrasound pulse, analog signal processing circuitry that combines echoes detected by transducers into a single analog echo signal, am analog-to-digital converter that converts the analog echo signal into a digital echo signal; and interface circuitry that transfers the digital echo signal across the passive interface cable to the host computer.

PRIORITY CLAIM

This application is a continuation of U.S. patent application Ser. No.13/951,807 entitled “PORTABLE ULTRASONIC IMAGING PROBE INCLUDING ATRANSDUCER ARRAY” filed Jul. 26, 2013 which claims the benefit ofpriority to U.S. Provisional Patent Application No. 61/676,193 filedJul. 26, 2012 entitled “PORTABLE ULTRASONIC IMAGING PROBE INCLUDING MEMSBASED TRANSDUCER ARRAY”, both of which applications are incorporatedherein by reference.

FIELD OF THE INVENTION

The present invention relates to portable ultrasonic imaging probes, andmore specifically, to such probes including transducer array, whereinsuch probes can be directly connected to a host computer, such as anoff-the-shelf laptop computer, or the like.

BACKGROUND

Typically, ultrasound imaging systems include a hand-held probe that isconnected by a cable to a relatively large and expensive piece ofhardware that is dedicated to performing ultrasound signal processingand displaying ultrasound images. Such systems, because of their highcost, are typically only available in hospitals or in the offices ofspecialists, such as radiologists. Recently, there has been an interestin developing more portable ultrasound imaging systems that can be usedwith personal computers. Preferably, such a portable ultrasound probecan be used with an off-the-shelf host computer, such as a personalcomputer, and is inexpensive enough to provide ultrasound imagingcapabilities to general practitioners and health clinics having limitedfinancial resources.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a high level diagram that is useful for describingembodiments of the present invention.

FIG. 1B illustrates a specific implementation of the inventionoriginally described with reference to FIG. 1A.

FIG. 2A is a block diagram that shows additional details of anultrasonic imaging probe according to an embodiment of the presentinvention.

FIG. 2B illustrates some further details of some of the blocksintroduced in FIG. 2A, according to an embodiment of the presentinvention.

FIG. 2C illustrates a perspective view of a probe head assembly,according to an embodiment of the present invention.

FIG. 2D illustrates how odd and even rows can be staggered relative toone another.

FIG. 3A is used to illustrate how sets of micromachined ultrasoundtransducers (MUTs) that collectively make up rings can be used to form aquasi-annular array transducer, and that such rings can be moved toemulate the mechanical movement of an annular array transducer, withoutrequiring any moving parts.

FIG. 3B is a blown-up view of two of the vectors shown in FIG. 3A.

FIGS. 4A-4D are used to illustrate a transmit sequence, according to anembodiment of the present invention.

FIGS. 5A-5D are used to illustrate a receive sequence, according to anembodiment of the present invention.

DETAILED DESCRIPTION

In the following detailed description, reference is made to theaccompanying drawings that form a part hereof, and in which is shown byway of illustration specific illustrative embodiments. It is to beunderstood that other embodiments may be utilized and that mechanicaland electrical changes may be made. The following detailed descriptionis, therefore, not to be taken in a limiting sense. In the descriptionthat follows, like numerals or reference designators will be used torefer to like parts or elements throughout. In addition, the first digitof a reference number identifies the drawing in which the referencenumber first appears.

FIG. 1A shows an ultrasonic imaging probe 102, according to anembodiment of the present invention, which is connected by a passiveinterface cable 106 to a host computer 112. Ultrasonic imaging probe 102includes an array of ultrasound transducers for transmitting andreceiving ultrasound pulses as will be described below. The hostcomputer 112 can be a desktop personal computer (PC), a laptop PC, apocket PC, a tablet PC, a mobile phone capable or running softwareprograms (often referred to as a “smart phone”), a personal digitalassistant, or the like. The passive interface cable 106, which includesconnectors and passive wires, can be a Universal Serial Bus (USB) cable(e.g., a USB 2.0 cable), a FireWre (also known as IEEE 1394) cable, orthe like. Preferably the probe 102 is not connected to any other deviceor power supply. Thus, in a preferred embodiment the probe 102 receivesall its necessary power from the host computer 112 via the passiveinterface cable 106. In alternative embodiments, probe 102 can include abattery and a wireless transceiver, in which case the probe can wirelesscommunicate with the host computer, and the probe can generate all itsnecessary power from the battery.

As will be described in more detail below, in accordance withembodiments of the present invention, the probe 102 enables the hostcomputer 112, via software running on the host computer 112, to formreal-time ultrasonic images of a target 100 (e.g., human tissue or othermaterials) without the need for any additional internal or externalelectronics, power supply, or support devices. In certain embodiments,the probe 102 produces raw digitized data that is envelope detectedultrasound echo data from an array of micromachined ultrasoundtransducers (MUTs) in the probe 102, and transmits such raw data to thehost computer 112. The raw digitized data can optionally also belogarithmically compressed, depending upon implementation. In anembodiment, when the host computer 112 receives raw data via the passiveinterface cable 106 from the probe 102, the host computer 112 performstime gain compensation (TGC), gray-scale mapping, and scan conversion ofthe raw data using software that runs on the host computer 112, anddisplays the resultant video images. The probe does not include anymoving mechanical parts, thereby reducing the complexity and cost of theprobe 102 and increasing its reliability. The term “raw data”, as usedherein, refers to ultrasound imaging data that has not yet been timegain compensated, gray-scale mapped and scan converted. As describedbelow, such raw data is included in the digital signal that istransferred from the probe 102 to the host computer 112.

As shown in FIG. 1A, the host computer 112 will likely include acommunications port 108, a communications chip-set 122, a centralprocessing unit (CPU) 124, memory 126, a display 128, and an inputdevice 130, such as a keyboard, mouse, touch screen, track ball, or thelike. Additionally, the host computer 112 runs software that enables thehost to control specific aspects of the probe 102. Such software alsoenables the host computer 112 to perform time gain compensation (alsoknown as time gain correction), gray-scale mapping, and scan conversionof the raw data received from the probe 112 over the passive interfacecable 106. The host computer 112 can then display the resultingultrasound video on the display 128, as well as store such video in itsmemory 126, or another data storage device (not shown). The article “ANew Time-Gain Correction Method for Standard B-Mode Ultrasound Imaging”,by William D. Richard, IEEE Transactions of Medical Imaging, Vol. 8, No.3, pp. 283-285, September 1989, which is incorporated herein byreference, describes an exemplary time gain correction technique thatcan be performed by the host computer 112. The article “Real-TimeUltrasonic Scan Conversation via Linear Interpolation of OversampledVectors,” Ultrasonic Imaging, Vol. 16, pp. 109-123, April 1994, which isincorporated herein by reference, describes an exemplary scan conversiontechnique that can be performed by the host computer 112. These are justexemplary details of the host computer 112, which are not meant to belimiting.

The passive interface cable 106 includes at least one data line overwhich data is carried, and at least one power line to provide power to aperipheral device, which in this case is the ultrasonic imaging probe102. For example, where the passive interface cable 106 is a USB 2.0cable, one wire of the cable provides about 5V at about ½ Amp. Inalternative embodiments, the passive interface cable 106 is a Firewirecable, which also includes a power wire. Other types of passiveinterface cable can be used if desired. However, as mentioned above, itis preferred that the passive interface cable 106 is a standardoff-the-shelf cable that can interface with an off-the-shelf interfaceIC. The term passive as used herein refers to a cable that does notregenerate signals or process them in any way. In an alternativeembodiment, the probe 102 and the host computer 112 communicatewirelessly, and the probe 102 includes a battery that is used to powerthe components within the probe.

FIG. 1B illustrates an example where the host computer 112 is a laptop.FIG. 1B also shows an exemplary ergonomic design of a housing 103 forthe ultrasonic imaging probe 102 of the present invention. Otherergonomic designs are of course possible, and within the scope of thepresent invention. Also, as explained above, other types of hostcomputer 112 can also be used. FIG. 1B also shows that the ultrasonicimaging probe 102 includes a probe head assembly 105.

In accordance with certain embodiments, the data samples produced by theultrasound imaging probe 102 of the present invention are transmitted bythe probe 102 across the interface cable 106 to the host computer 112.In a specific embodiment, this is accomplished when the host computer112 reads the data temporarily stored in the buffers of the interface IC204. The host computer 112 runs software that enables the host toperform time gain compensation (TGC), gray-scale mapping, and scanconversion of the data received from the probe 102, and the hostdisplays the resultant video images. Advantageously, the host computer112 does not need to perform electronic beamforming or other equivalentimage processing, thereby simplifying the software that the hostcomputer 112 runs.

The host computer 112 can use the digital data received from theultrasound device 102 to provide any available type of ultrasoundimaging mode can be used by the host computer 112 to display theultrasound images, including, but not limited to A-mode, B-mode, M-mode,etc. For example, in B-mode, the host computer 112 performs know scanconversion such that the brightness of a pixel is based on the intensityof the echo return.

A benefit of specific embodiments of the present invention is that onlydigital signals are transmitted from the probe 102 to the host computer112, thereby providing for better signal-to-noise ratio than if analogsignals were transmitted from the probe 102 to the host computer 112, orto some intermediate apparatus between the host computer and the probe.Another benefit of specific embodiments of the present invention is thatthe probe 102 can be used with a standard off-the-shelf passiveinterface cable.

A further benefit of specific embodiments of the present invention isthat the probe 102 does not perform any time gain compensation,gray-scale mapping and scan conversion, thereby significantly decreasingthe complexity, power requirements and cost of the probe 102.Conventionally, functions such as scan conversion, time gain correction(also known as time gain compensation) and gray-scale mapping areperformed by a machine that is dedicated to obtaining ultrasound images,or by an intermediate device that is located between the probe and hostcomputer. In contrast, here software running on the host computer 112 isused to perform these functions, thereby reducing the complexity andcost of the portable ultrasonic imaging probe 102.

FIG. 2A is a block diagram that shows additional details of anultrasonic imaging probe according to an embodiment of the presentinvention. Additional details of the ultrasonic imaging probe 102,according to specific embodiments of the present invention, shall now bedescribed with reference FIG. 2A. As shown in FIG. 2A, in accordancewith an embodiment of the present invention, the probe 102 includes aperipheral connector 104 and an interface IC 204 that enables the probe102 to interface with the host computer 112 via the interface cable 106.The connector 104 and the interface IC 204 are preferably off-the-shelfdevices, but can be custom devices.

In accordance with an embodiment illustrated in FIG. 2A, specificcertain components (shown within a large dash-lined rectangle) arelocated within the probe head assembly 105, with the remainingcomponents being within the housing 103 of the ultrasonic imaging probe102. An interface cable 209 connects the components within the housing103 to the components within the probe head assembly 105.

The probe 102 is also shown as including a digital control andprocessing block 206, an analog to digital converter (ADC) 208 and ahigh voltage power supply (HVPS) 250. The HVPL 250 provides power to ahigh voltage (HV) pulser 224. Additionally, the probe 102 is shown asincluding a micromachined ultrasound transducer (MUT) array 220, whichincludes individually controllable MUT elements 221, which are discussedin additional detail below. A transmit and receive (Tx/Rx) controller240 accesses vector configuration and timing data stored within a memory230 in order to controls transmit (Tx) switches 222 and receive (Rx)switches 216, to thereby control the operation of the MUT elements 221of the array 220, as described in additional detail below. In certainembodiments, such vector configuration and timing data is stored withina look-up table (LUT) within the memory 230.

The probe 102 also includes analog summing, amplification and processingcircuitry 215. In accordance with an embodiment, the analog summing,amplification and processing circuitry 215 includes summing resistors214 and a summing amplifier 212, which are discussed in more detail withreference to FIG. 2B, and an analog signal processing block 210. Theanalog signal processing block 210 can include, e.g., a pre-amplifier, afilter (e.g., a low pass or bandpass filter) and an envelope detector,and optionally a logarithmic amplifier. Such a pre-amplifier can be,e.g., a very low noise amplifier that provides about 20 dB of gain. Thefilter can filter out frequencies that are not of interest. The summingresistors 214 and the summing amplifier 212 combine numerous echosignals (received using numerous MUT elements) into a single echosignal. In accordance with an embodiment, this single echo signal ispre-amplified, filtered (e.g., low pass filtered) and envelope detectedto produce a radio frequency (RF) signal. Logarithmic compression can beperformed within the analog signal processing block 210, or within thedigital control and processing block 210, or alternatively, within thehost computer 112.

The RF signal output by the analog signal processing block 210 isdigitized by the ADC 208. The ADC 208 samples the RF signal (e.g., at 30or 48 MHz), to thereby digitize the signal, and provides the digitizedsignal to the digital control and processing block 210. The digitalcontrol and processing block 206 could be implemented, e.g., using acomplex programmable logic device (CPLD), a field-programmable gatearray (FPGA), an application specific integrated circuit (ASIC) or someother circuitry. The digital control and processing clock 206 controlfunctions and timing of the hardware in the probe, and depending uponimplementation, can also perform digital signal processing of thedigital signal output by the ADC 208. For example, the digital controland processing block 206 can perform logarithmic compression, as wasmentioned above. The digital control and processing clock 206 alsocontrols the Tx/Rx controller 240.

The Tx/Rx controller 240, which can be implemented using an FPGA, anASIC or some other circuitry, controls the Tx switches 222 so that aselected set of the MUTs transmit ultrasonic pulses generated by a highvoltage (HV) pulser 224. The host computer 112, through the passiveinterface cable 106, and the interface IC 204 can control the amplitude,frequency and duration of the pulses output by the HV pulser 224. Forexample, the host computer 112 can write vector configuration and timingdata to the memory 230. Additionally, the host computer 112 can sendinstructions to the probe 102 that cause the probe 102 to select, fromthe memory 230, specific transmit and receive vector control and timingdata used to control transmission and reception of ultrasonic pulses.

The HV pulser 224 is powered by the HVPS 250, which generates the highvoltage potential(s) required by the HV pulser 224 from a lower voltage(e.g., 5V) received via the passive interface cable 106. Depending uponimplementation, the HV pulser 224 can produce unipolar pulses, orbipolar pulses. Unipolar pulses can be, e.g., high voltage pulses thatare as large as 100V. Where the HV pulser 224 produces bipolar pulses,the HV pulser 224 may produce, e.g., both positive and negative highvoltage pulses that can be as large as +/−100V. In such embodiments, theHVPS 250 can provide up to +/−100V supply rails to the HV pulser 224.Exemplary details of an HVPS, which can be used to implement the HVPS250, are shown in and described with reference to FIG. 4 of U.S. PatentPublication No. 2007/0239019, which is incorporated herein by reference.

The probe 102 can also include a linear regulator IC (now shown) withintegrated power switches and low quiescent current requirementsdesigned for USB applications. For example, such a linear regular IC canproduce a 3.3V digital supply and a 3.3V analog voltage supply, whichare used to provide power to the various circuits/blocks within theprobe 102. For example, a 3.3V digital supply can power the interface IC204 and the digital control and processing block 206; and a 3.3V analogsupply can power the summing amplifier 212 and the analog signalprocessing circuitry 210. An exemplary IC that can be used for thelinear regulator IC is the TPS2148 3.3-V LDO and Dual Switch for USBPeripheral Power Management IC, available from Texas Instruments ofDallas, Tex.

Preferably, the probe 102 is configured as a single channelarchitecture, which means that only a single ADC 208 is required, andonly a single data signal is transmitted from the probe 102 to the host112 at any given time. However, in alternative embodiments, a multiplechannel architecture that includes multiple ADCs can be implemented.Unless stated otherwise, the embodiments described herein include asingle channel architecture.

Another benefit of specific embodiments of the present invention is thatthe MUT array 220 is in close proximity to (i.e., within the samehousing as) the analog summing, amplifying and processing circuitry 215and the ADC 208. This will provide for good signal-to-noise (S/N) ratio,as compared to systems where the analog signals output by thetransducers must travel across a relatively long distance before theyare amplified and/or digitized.

As mentioned above, the portable ultrasound imaging probe 102 includes amicromachined ultrasound transducer (MUT) array 220, which includesnumerous MUTs 221, each of which can be referred to as an MUT element(or simply as an MUT). Such an MUT array 220, which can also be referredto as an array of MUTs, is an example of a MEMS based transducer, sincethe MUTs are examples of micro-electro-mechanical systems (MEMS). EachMUT element can include a single MUT cell, or multiple MUT cellshardwired together.

Each MUT cell can be a capacitive MUT (cMUT) cell or a piezoelectric MUT(pMUT) cell, but is not limited thereto. Such cells typically include amembrane (often referred to as a diaphragm) and two or more electrodes.For transmission, the electrodes and membrane are used to modulate acapacitive charge that vibrates the membrane and thereby transmits asound wave. For reception, the electrodes and membrane are used toconvert the sound vibration of a received ultrasound signal into amodulated capacitance. More specifically, when an AC signal is appliedacross the electrodes, the MUT generates ultrasonic waves in the mediumof interest to thereby function as a transmitter. When ultrasonic wavesare applied to the membrane of a MUT, the MUT generates an alternatingsignal as the capacitance of the MUT is varied to thereby function as areceiver of ultrasonic waves. Each MUT element can simply be referred toas an MUT, and a plurality of MUT elements can simply be referred to asMUTs. Preferably, the MUT array 220 is encased in material that has theproper acoustic impedance to be matched with acoustic impedance of humantissue.

Advantageously, MUTs can be made using semiconductor fabricationprocesses, such as microfabrication processes generally referred to as“micromachining”. Micromachining is the formation of microscopicstructures using patterning, deposition and/or etching. Patterninggenerally includes lithography, which can be performed usingprojection-aligners or wafer-steppers, but is not limited thereto.Deposition can be physical vapor deposition (PVD), chemical vapordeposition (CVD), low-pressure chemical vapor deposition (LPCVD), orplasma chemical vapor deposition (PECVD), but is not limited thereto.Etching can include wet-chemical etching, plasma-etching, ion-milling,sputter-etching or laser-etching, but is not limited thereto.

Micromachining is typically performed on substrates or wafers made ofsilicon, glass, sapphire or ceramic. Such substrates or wafers aregenerally very flat and smooth and have lateral dimensions in inches.They are usually processed as groups in cassettes as they travel fromprocess tool to process tool. Each substrate can advantageously (but notnecessarily) incorporate numerous copies of a product. Micromachiningcan include the use of conventional or known micromachinable materialsincluding silicon, sapphire, glass materials of all types, polymers(such as polyimide), polysilicon, silicon nitride, silicon oxynitride,thin film metals such as aluminum alloys, copper alloys and tungsten,spin-on-glasses (SOGs), implantable or diffused dopants and grown filmssuch as silicon oxides and nitrides, but is not limited thereto.

In accordance with an embodiment, the MUT array 220 includes M rows×Ncolumns of transducer elements, with the MUTs 221 being illustrated assmall circles in FIG. 2A. For example, if M=20 and N=100, then the MUTarray would include 2000 MUTs. In accordance with an embodiment, half ofthe MUTs 221 can be selectively used for transmitting ultrasonic pulses,and the other half of the MUTs 221 can be selectively used for receiving“echo pulses”. Continuing with the example where the MUT array 220includes 2000 MUTs, then 1000 of the MUTs 221 can be can be selectivelyused for transmitting ultrasonic pulses, and 1000 of the MUTs 221 can beselectively used for receiving “echo pulses”. More generally, P1 percentof the MUTs can be selectively used for transmitting ultrasonic pulses,and P2 percent (where P2=100%−P1) of the MUTs can be selectively usedfor receiving “echo pulses”. Unless specified otherwise, it will beassumed that P1=P2=50%, such that half of the MUTs can be selectivelyused for transmitting ultrasonic pulses, and half of the MUTs can beselectively used for receiving “echo pulses”.

For illustrative purposes, the MUTs that can be used for transmittingultrasonic pulses, which can be referred to as Tx MUTs, are illustratedin FIG. 2A as small filled circles 223; and the MUTs that can be usedfor receiving ultrasonic pulses, which can be referred to as Rx MUTs,are illustrated in FIG. 2A as small unfilled circles 225.

Each of the MUTs 221 can have a circumferential shape that is circular,as shown. Each MUT 221 can be, e.g., about 50 micrometers in diameter,but is not limited thereto. The distance from the edge of one MUT 221 toits closest adjacent MUT 221 can be, e.g., about 70 micrometers, but isnot limited thereto. Alternatively, each of the MUTs can have anothercircumferential shape, including, but not limited to, square orhexagonal. In accordance with certain embodiments, the Tx MUTs 223 andthe Rx MUTs 225 are structurally the same. In such embodiments, the onlydifference between a Tx MUT 223 and an Rx MUT 225 is how the MUT isconnected to other circuitry and used. In other embodiments, the Tx MUTs223 can be structurally different from the Rx MUTs 225.

All of the rows and columns can be inline with one another, as shown inFIG. 2A. Alternatively, odd rows can be staggered relative even rows, asshown in FIG. 2D. It is also possible that odd columns be staggeredrelative to even columns. Other variations are also possible, and withinthe scope of an embodiment of the present invention. In the embodimentshown in FIG. 2A, the Tx MUTs 223 and the Rx MUTs 225 alternate in a waythat creates minimum pitch in linear array configuration, therebyenabling better lateral resolution.

As will be described in further detail below, at any given time, a setof the Tx MUTs 223 can be selected for transmitting ultrasonic pulses,and a set of the Rx MUTs 225 can be selected for receiving echo pulses.For example, sets of Tx MUTs 223 that collectively make up rings can beused to form a quasi-annular array transducer, as will be describedbelow with reference to FIGS. 3-5. Switches 222, which can be referredto as Tx switches 222, can be used to select which Tx MUTs 223 areactive at a time. Similarly, switches 216, which can be referred to asRx switches, can be used to select which Rx MUTs 225 are active at atime. In accordance with an embodiment, each of the Tx MUTs 223 isconnected to a corresponding Tx switch. When the Tx switch is turned on(which can also be referred to as closed), the Tx MUT 223 is connectedby its corresponding Tx switch to the HV pulser 224, thereby causing theTx MUT 223 to output an ultrasonic pulse. When multiple MUTs 223 aretriggered simultaneously (i.e., simultaneously connected by switches tothe HV pulser 224), the multiple MUTs collectively produce an ultrasonicpulse or wave-front.

Selected Tx MUTs 223 transmit ultrasonic pulses into the target regionbeing examined, and selected Rx MUTs 225 receive reflected ultrasonicpulses (i.e., “echo pulses”) returning from the region. Whentransmitting, the selected Tx MUTs 223 are excited to high-frequencyoscillation by the pulses emitted by the HV pulser 224, therebygenerating ultrasound pulses that can be directed at a targetregion/object to be imaged.

These ultrasound pulses (also referred to as ultrasonic pulses) producedby the selected Tx MUTs 223 are echoed back towards the selected Rx MUTs225 from some point within the target region/object, e.g., at boundarylayers between two media with differing acoustic impedances. The echopulses received by the selected Rx MUTs 225 are converted intocorresponding low-level electrical input signals (i.e., the “echosignals”) that are provided to the analog summing, amplification andprocessing circuitry 215. In specific embodiments, to receive echopulses, the Rx switches 216 selectively connect a set of the Rx MUTs 225to summing resistors 214, which are used to sum the echo pulses at theinput of a summing amplifier 212.

FIG. 2B illustrates some further details of some of the blocksintroduced in FIG. 2A, according to an embodiment of the presentinvention. Exemplary details of the Rx switches 216, the summingresistors 214 and the summing amplifier 212 are shown in FIG. 2B. Theanalog summing, amplification and processing circuitry 215 includessumming resistors 214 and a summing amplifier 212.

FIG. 2C illustrates a perspective view of the probe head assembly 105,according to an embodiment of the present invention. FIG. 2C also showsa portion of the interface cable 209, which is used to connect thecomponents within the probe head assembly 105 to components within theprobe housing 103.

FIG. 2D illustrates how odd and even rows can be staggered relative toone another. All of the rows and columns can be inline with one another,as shown in FIG. 2A. Alternatively, odd rows can be staggered relativeeven rows, as shown in FIG. 2D. It is also possible that odd columns bestaggered relative to even columns. Other variations are also possible,and within the scope of an embodiment of the present invention. In theembodiments shown in FIGS. 2A, 3A and 3B, the Tx MUTs 223 and the RxMUTs 225 alternate in a way that creates minimum pitch in linear arrayconfiguration, there by enabling better lateral resolution.

FIG. 3A is used to illustrate how sets of micromachined ultrasoundtransducers (MUTs) that collectively make up rings can be used to form aquasi-annular array transducer, and that such rings can be moved toemulate the mechanical movement of an annular array transducer, withoutrequiring any moving parts. As mentioned above, sets of Tx MUTs 223 thatcollectively make up rings can be used to form a quasi-annular arraytransducer, as will now be described below with reference to FIGS. 3-5.Referring to FIG. 3A, illustrated therein are a plurality of possibleMUT vectors, each of which is made up of a plurality of annularrings/circles of MUTs 221. Each such vector can be made up of aplurality of different sets of MUTs 221, wherein each set of MUTsdefines a different annular ring/circle of MUTs 221, as can beappreciated from the discussion of FIGS. 4A-4D below.

Still referring to FIG. 3A, illustrated therein are four different MUTvectors, the first one of which is labeled Vector 1, and the last one ofwhich is labeled Vector X. If, e.g., X=128, that would mean that 128 ofthe annular array MUT vectors can be produced using the MUT array 220.More specifically, by controlling the Tx and Rx switches 222 and 216 (inFIG. 2A), the various MUT Vectors (1 through 128) can be selected, oneafter the other, to emulate an annular array that is mechanically movedthrough 128 different physical positions. However, here there is nomechanical movement; but rather, different MUTs are selected to emulatethe movement. FIG. 3B is a blown-up view of two of the closely spacedadjacent vectors shown in FIG. 3A.

FIG. 3B is a blown-up view of two of the vectors shown in FIG. 3A. As,shown, in the embodiments shown in FIGS. 3A and 3B, the Tx MUTs 223 andthe Rx MUTs 225 alternate in a way that creates minimum pitch in lineararray configuration, thereby enabling better lateral resolution.

FIGS. 4A-4D will now be used to illustrate how a transmit MUT vector canbe used to transmit focused ultrasound beams. FIGS. 4A-4D are used toillustrate a transmit sequence, according to an embodiment of thepresent invention. FIGS. 4A-4D illustrates different sized rings of TxMUTs 223, which can collectively be used to generate one focusedultrasound beam. More specifically, the ring of Tx MUTs shown in FIG. 4Acan be used to collectively transmit a first ultrasound pulse; a shortprogrammed delay thereafter the ring of Tx MUTs shown in FIG. 4B can beused to collectively transmit a second ultrasound pulse; a shortprogrammed delay thereafter the ring of Tx MUTs shown in FIG. 4C can beused to collectively transmit a third ultrasound pulse; and a shortprogrammed delay thereafter the ring of Tx MUTs shown in FIG. 4D can beused to collectively transmit a fourth ultrasound pulse. These fourultrasound pulses, as mentioned above, collectively make up a focusedultrasound beam.

The ring in FIG. 4A has the largest aperture, and the ring in FIG. 4Dhas the smallest/no aperture. In FIGS. 4A-4D, the four different ringsshown therein do not overlap one another. However, in alternativeembodiments, there can be overlap between the different rings. In otherwords, a Tx MUT can be included in more than one annular ring.

FIGS. 5A-5D illustrate how a receive MUT vector can be used to receiveecho pulses generated in response to the focused ultrasound beam FIGS.5A-5D illustrate different sized rings of Rx MUTs 225, which cancollectively be used to receive echo pulses and produce an echo signal.More specifically, the ring of Rx MUTs 225 shown in FIG. 5A can be usedto collectively receive a first echo pulse; a short programmed delaythereafter the ring of Rx MUTs shown in FIG. 5B can be used tocollectively receive a second echo pulse; a short programmed delaythereafter the ring of Rx MUTs shown in FIG. 5C can be used tocollectively receive a third echo pulse; and a short programmed delaythereafter the ring of Rx MUTs shown in FIG. 5D can be used tocollectively receive a fourth echo pulse. These four echo pulsescollectively make up a received ultrasound echo.

The circle of Rx MUTs in FIG. 5A, which has the smallest aperture, willreceive near field echoes. By contrast, the circle of Rx MUTs in FIG.5D, which has the largest aperture, will receive the deepest fieldechoes. In FIGS. 5A-5D, the four different circles shown therein overlapone another. Further, it is noted that sets of the Rx MUTs can beselected in such a way that the active area of the circular arrays cancontinuously increase with a controlled number of sampling cycles inorder to optimize the resolution of the received signal from differentdepths.

In accordance with certain embodiments of the present invention,preprogrammed vector configuration and timing data that enables thevarious annular rings shown in FIGS. 4A-4D to be fired in sequence isstored in the memory 230, e.g., in a LUT. Similar data used the controlsreception, as was described with reference to FIGS. 5A-5D, is alsostored in the memory 230. Advantageously, the MUT array 220 and thecircuitry used to select sets of the MUTs can provide a continuouslyvariable aperture annular array. More specifically, such circuitry canbe used to activate sets of MUTs in such a way that the active area ofannular arrays will continuously shift in order to form ultrasound beamswith variable focal points. In other words, the MUT array 220 can beused to perform beam forming and aperture control for each of aplurality of different MUT vectors. Advantageously, beam shapes can beoptimized for both transmit and receive signals.

While the Tx MUT and Rx MUT vectors shown in FIGS. 4A-4D and 5A-5Dinclude substantially circular annular arrays, because of theflexibility provided by the MUT array 220, the vectors can havealternative shapes, such as, but not limited to elliptical shapes. Inalternative embodiments, the Tx MUTs and Rx MUTs can be selectivelyconnected to produce other types of arrays, besides annular arrays.

In alternative embodiments, rather than having half the MUTs 221dedicated to functioning as Tx MUTs 223, and half the MUTs 221dedicating to functioning as Rx MUTs 225, each of the MUTs 221 of theMUT array 220 can be capable of being used as either an Rx MUT 223 or aTx MUT 225. In such alternative embodiments, transmit/receive (Tx/Rx)switches can be used in place Tx switches 222 and the Rx switches 216,and the Tx/Rx switches can be used to connect a selected set of the MUTsto either the pulser 224 or the analog summing, amplification andprocessing circuitry 215. When a high voltage pulse is produced by thepulser 224, the Tx/Rx switches would automatically block the highvoltage from damaging the analog summing, amplification and processingcircuitry 215. When the HV pulser 224 is not producing a pulse, theTx/Rx switches would disconnect the selected set of MUTs from the pulser224, and to connect the selected set of MUTs to the analog summing,amplification and processing circuitry 215. However, the aforementionedembodiments where certain MUTs are dedicated to transmission, and otherMUTs are dedicated to reception, such a configuration eliminates theneed Tx/Rx switches, which are relatively expensive.

The foregoing description of preferred embodiments of the presentinvention has been provided for the purposes of illustration anddescription. It is not intended to be exhaustive or to limit theinvention to the precise forms disclosed. Many modifications andvariations will be apparent to one of ordinary skill in the relevantarts. The above mentioned part numbers are exemplary, and are not meantto be limiting. Accordingly, other parts can be substituted for thosementioned above.

The embodiments were chosen and described in order to best explain theprinciples of the invention and its practical application, therebyenabling others skilled in the art to understand the invention forvarious embodiments and with various modifications that are suited tothe particular use contemplated. It is intended that the scope of theinvention be defined by the claims and their equivalents.

What is claimed is:
 1. An ultrasound system comprising: a portableultrasound imaging probe; a probe head mounted on the probe including anarray comprising a plurality of ultrasound transmitting ultrasoundtransducers (Tx transducers) and a plurality of ultrasound receivingultrasound transducers (Rx transducers); a high voltage (HV) pulserwithin the probe; an analog summing amplifier within the probe; aplurality of transmit (Tx) switches within the probe, wherein each ofthe plurality of Tx switches connects the HV pulser and a different oneof the plurality of Tx transducers; a plurality of receive (Rx) switcheswithin the probe, wherein each of the plurality of Rx switches connectsa different one of the plurality of Rx transducers to the analog summingamplifier; wherein the plurality of Tx switches is not connected to theplurality of Rx transducers, and the plurality of Rx switches is notconnected to the plurality of Tx transducers whereby the Rx transducersare never used to emit ultrasound; a controller within the probe andcoupled to the plurality of Tx switches and plurality of Rx switches;wherein the controller is configured to selectively close the Txswitches to connect transmit sets of the Tx transducers to the HV pulserincluding a first transmit set of the transmit sets of the Txtransducers at a first transmit time, a second transmit set of thetransmit sets of the Tx transducers at a second transmit time, and athird transmit set of the transmit sets of the Tx transducers at a thirdtransmit time; and the controller is configured to selectively close theRx switches to connect receive sets of the Rx transducers to the analogsumming amplifier including a first receive set of the receive sets ofthe Rx transducers at a first receive time, a second receive set of thereceive sets of the Rx transducers at a second receive time, and a thirdreceive set of the receive sets of the Rx transducers at a third receivetime; wherein the analog summing amplifier combines echoes detected bythe receive sets of ultrasound transducers into an analog echo signalwhich is output by the analog summing amplifier; an analog-to-digitalconverter (ADC) within the probe that converts the analog echo signaloutput by the analog summing amplifier, to a digital echo signal; aninterface cable configured to connect the probe to a host computer; andinterface circuitry within the probe that transfers the digital echosignal through the interface cable to the host computer.
 2. Theultrasound system of claim 1, wherein the probe consumes at most 2.5Watts of power.
 3. The ultrasound system of claim 1, wherein: the firsttransmit set of Tx transducers is at a first position within said array,the second transmit set of Tx transducers is at a second position withinsaid array, and the third transmit set of Tx transducers is at a thirdposition within said array, such that the probe head emits an ultrasoundbeam from the first position within the array at the first time, thesecond position within the array at the second time, and the thirdposition within the array at the third time without moving the probehead.
 4. The ultrasound system of claim 1, wherein: the first receiveset of Rx transducers is at a first position within said array, thesecond transmit set of Rx transducers is at a second position withinsaid array, and the third receive set of Rx transducers is at a thirdposition within said array, such that the probe head receives ultrasoundechoes from the first position within the array at the first time, thesecond position within the array at the second time, and the thirdposition within the array at the third time without moving the probehead.
 5. The ultrasound system of claim 1, wherein: the first transmitset of Tx transducers have a first annular distribution within saidarray, the second transmit set of Tx transducers have a second annulardistribution within said array having a smaller aperture than the firsttransmit set of Tx transducers, and the third transmit set of Txtransducers have a third annular distribution within said array having asmaller aperture than the second transmit set of Tx transducers; andwhereby the array of ultrasound transducers operates as a variableaperture ultrasound transmitter.
 6. The ultrasound system of claim 1,wherein: the first set Rx transducers is smaller than the second set ofRx transducers, which is smaller than the third set of Rx transducers,such that the set of Rx transducers connected to the analog summing,amplification and signal processing circuitry increases in size overtime; whereby the array of ultrasound transducers operates as a variableaperture ultrasound receiver.
 7. The ultrasound system of claim 1,wherein: the first receive set of Rx transducers have a first circulardistribution within said array, the second receive set of Rx transducershave a second circular distribution within said array having a largerdiameter than the first receive set of Rx transducers, and the thirdreceive set of Rx transducers have a third circular distribution withinsaid array having a larger diameter than the second receive set of Rx;transducers, in order to enhance resolution of ultrasound echoes fromdifferent depths.
 8. The ultrasound system of claim 1, furthercomprising the host computer connected to the probe by the interfacecable wherein: the host computer receives the digital echo signal fromthe interface circuitry; and wherein the host computer is configured toperform digital processing of the digital echo signal received from theprobe and display ultrasound images on a display associated with thehost computer.
 9. The ultrasound system of claim 1, further comprisingthe host computer connected to the probe by the interface cable wherein:the host computer provides power to operate the probe via the interfacecable; the host computer receives the digital echo signal from theinterface circuitry; and wherein the host computer is configured toperform digital processing of the digital echo signal received from theprobe and display ultrasound images on a display associated with thehost computer.
 10. The ultrasound system of claim 1, wherein: thecontroller is configured to selectively close the Tx switches to connecttransmit sets of the Tx transducers to the HV pulser and close the Rxswitches to connect receive sets of the Tx transducers to the analogsumming amplifier using vector configuration and timing data storedwithin a memory within the probe.
 11. The ultrasound system of claim 10,in combination with the host computer connected to the probe by theinterface cable wherein: the host computer is configured to sendinstructions to the probe via the interface cable that cause thecontroller to select, from the memory, specific vector configuration andtiming data to control transmitting and receiving of ultrasound by theprobe.
 12. The ultrasound system of claim 10, in combination with thehost computer connected to the probe by the interface cable wherein: thehost computer is configured to write vector configuration and timingdata to the memory via the interface cable.
 13. The ultrasound system ofclaim 1, wherein the Tx transducers and the Rx transducers comprisemicro-machined ultrasound transducers (MUTs) machined in rows andcolumns on a common substrate to form the array.
 14. An ultrasoundsystem comprising: a portable ultrasound imaging probe; a probe headmounted on the probe including an array comprising a plurality ofultrasound transmitting ultrasound transducers (Tx transducers) and aplurality of ultrasound receiving ultrasound transducers (Rxtransducers); a high voltage (HV) pulser within the probe; an analogsumming amplifier within the probe; a plurality of transmit (Tx)switches within the probe, wherein each of the plurality of Tx switchesis connected between the HV pulser and a different one of the pluralityof Tx transducers; a plurality of receive (Rx) switches within theprobe, wherein each of the plurality of Rx switches is connected betweena different one of the plurality of Rx transducers and the analogsumming amplifier; wherein the plurality of Rx switches and Rxtransducers are isolated from the HV pulser and are never used to emitultrasound; a controller within the probe and coupled to the pluralityof Tx switches and plurality of Rx switches; wherein the controller isconfigured to selectively close the Tx switches to connect transmit setsof the Tx transducers to the HV pulser including a first transmit set ofthe transmit sets of the Tx transducers at a first transmit time, asecond transmit set of the transmit sets of the Tx transducers at asecond transmit time, and a third transmit set of the transmit sets ofthe Tx transducers at a third transmit time; and the controller isconfigured to selectively close the Rx switches to connect receive setsof the Rx transducers to the analog summing amplifier including a firstreceive set of the receive sets of the Rx transducers at a first receivetime, a second receive set of the receive sets of the Rx transducers ata second receive time, and a third receive set of the receive sets ofthe Rx transducers at a third receive time; wherein the analog summingamplifier combines echoes detected by the receive sets of ultrasoundtransducers into an analog echo signal which is output by the analogsumming amplifier; an analog-to-digital converter (ADC) within the probethat converts the analog echo signal output by the analog summingamplifier, to a digital echo signal; an interface cable; and interfacecircuitry within the probe that transfers the digital echo signalthrough the interface cable.
 15. The ultrasound system of claim 14,wherein the probe consumes at most 2.5 Watts of power.
 16. Theultrasound system of claim 14, wherein: the controller is configured toselectively close the Tx switches to connect transmit sets of the Txtransducers to the HV pulser and close the Rx switches to connectreceive sets of the Tx transducers to the analog summing amplifier usingvector configuration and timing data stored within a memory within theprobe.
 17. The ultrasound system of claim 14, further comprising a hostcomputer connected to the probe by the interface cable wherein: the hostcomputer receives the digital echo signal from the interface circuitry;and wherein the host computer is configured to perform digitalprocessing of the digital echo signal received from the probe anddisplay ultrasound images on a display associated with the hostcomputer.
 18. The ultrasound system of claim 17 wherein: the hostcomputer is further configured to send instructions to the probe via theinterface cable that cause the controller to select, from the memory,specific vector configuration and timing data to control transmittingand receiving of ultrasound by the probe.
 19. The ultrasound system ofclaim 17 wherein: the host computer is further configured to writevector configuration and timing data to the memory via the interfacecable.
 20. The ultrasound system of claim 17 wherein: the host computerprovides power to operate the probe via the interface cable.
 21. Theultrasound system of claim 14, wherein: the first transmit set of Txtransducers is at a first position within said array, the secondtransmit set of Tx transducers is at a second position within saidarray, and the third transmit set of Tx transducers is at a thirdposition within said array, such that the probe head emits ultrasoundfrom the first position within the array at the first time, the secondposition within the array at the second time, and the third positionwithin the array at the third time without moving the probe head. 22.The ultrasound system of claim 14, wherein: the first receive set of Rxtransducers is at a first position within said array, the secondtransmit set of Rx transducers is at a second position within saidarray, and the third receive set of Rx transducers is at a thirdposition within said array, such that the probe head receives ultrasoundechoes from the first position within the array at the first time, thesecond position within the array at the second time, and the thirdposition within the array at the third time without moving the probehead.
 23. The ultrasound system of claim 14, wherein: the first transmitset of Tx transducers have a first annular distribution within saidarray, the second transmit set of Tx transducers have a second annulardistribution within said array having a smaller aperture than the firsttransmit set of Tx transducers, and the third transmit set of Txtransducers have a third annular distribution within said array having asmaller aperture than the second transmit set of Tx transducers; andwhereby the array of ultrasound transducers operates as a variableaperture ultrasound transmitter.
 24. The ultrasound system of claim 14,wherein: the first set Rx transducers is smaller than the second set ofRx transducers, which is smaller than the third set of Rx transducers,such that the set of Rx transducers connected to the analog summing,amplification and signal processing circuitry increases in size overtime; whereby the array of ultrasound transducers operates as a variableaperture ultrasound receiver.
 25. The ultrasound system of claim 14,wherein: the first receive set of Rx transducers have a first circulardistribution within said array, the second receive set of Rx transducershave a second circular distribution within said array having a largerdiameter than the first receive set of Rx transducers, and the thirdreceive set of Rx transducers have a third circular distribution withinsaid array having a larger diameter than the second receive set of Rx;transducers, in order to enhance resolution of ultrasound echoes fromdifferent depths.
 26. The ultrasound system of claim 14, wherein the Txtransducers and the Rx transducers comprises micro-machined ultrasoundtransducers (MUTs) machined in rows and columns on a common substrate.